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WO2011158848A1 - Dispositif de tomographie optique et procédé de tomographie optique - Google Patents

Dispositif de tomographie optique et procédé de tomographie optique Download PDF

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Publication number
WO2011158848A1
WO2011158848A1 PCT/JP2011/063640 JP2011063640W WO2011158848A1 WO 2011158848 A1 WO2011158848 A1 WO 2011158848A1 JP 2011063640 W JP2011063640 W JP 2011063640W WO 2011158848 A1 WO2011158848 A1 WO 2011158848A1
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Prior art keywords
image
signal
light
unit
signal area
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PCT/JP2011/063640
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English (en)
Japanese (ja)
Inventor
和弘 広田
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Fujifilm Corp
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Fujifilm Corp
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0062—Arrangements for scanning
    • A61B5/0066—Optical coherence imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7235—Details of waveform analysis
    • A61B5/7253—Details of waveform analysis characterised by using transforms
    • A61B5/7257—Details of waveform analysis characterised by using transforms using Fourier transforms
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/47—Scattering, i.e. diffuse reflection
    • G01N21/4795—Scattering, i.e. diffuse reflection spatially resolved investigating of object in scattering medium
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N2021/178—Methods for obtaining spatial resolution of the property being measured
    • G01N2021/1785—Three dimensional
    • G01N2021/1787—Tomographic, i.e. computerised reconstruction from projective measurements

Definitions

  • the present invention relates to an optical tomographic imaging apparatus and an optical tomographic imaging method, and more particularly to an optical tomographic imaging apparatus and an optical tomographic imaging method capable of clearly identifying a region where light is not detected in a tomographic image.
  • OCT optical coherence tomography
  • This OCT measurement has an advantage that the resolution is about 10 ⁇ m higher than that of ultrasonic measurement, and a detailed tomographic image inside the living body can be obtained.
  • a three-dimensional tomographic image can be obtained by acquiring a plurality of images while shifting the position in a direction perpendicular to the tomographic image.
  • frequency domain OCT Frequency domain OCT
  • Patent Document 3 there is a technique for specifying a pixel position corresponding to a layer boundary by applying a differential filter in the depth direction after performing preprocessing (smoothing, averaging processing, etc.) on image data.
  • Typical examples of apparatus configurations that perform frequency domain OCT (Frequency domain OCT) measurement include SD-OCT (Spectral Domain OCT) apparatus and SS-OCT (Swept Source OCT).
  • the SD-OCT device uses broadband low-coherent light such as SLD (Super Luminescence Diode) or ASE (Amplified Spontaneous Emission) light source, white light as a light source, and uses a Michelson interferometer or the like to generate broadband low-coherent light. After splitting into measurement light and reference light, irradiate the measurement light on the object to be measured, cause the reflected light and reference light that have returned at that time to interfere with each other, and decompose this interference light into frequency components using a spectrometer.
  • SLD Super Luminescence Diode
  • ASE Ampliclified Spontaneous Emission
  • the interference light intensity for each frequency component is measured using a detector array in which elements such as photodiodes are arranged in an array, and the spectrum interference intensity signal obtained thereby is Fourier transformed by a computer to obtain an optical signal.
  • a tomographic image is constructed.
  • the SS-OCT apparatus uses a laser that temporally sweeps the optical frequency as a light source, causes reflected light and reference light to interfere with each other at each wavelength, and measures the time waveform of the signal corresponding to the temporal change of the optical frequency.
  • An optical tomographic image is constructed by Fourier-transforming the spectral interference intensity signal thus obtained with a computer.
  • OCT measurement is a method for acquiring an optical tomographic image of a specific region as described above.
  • an endoscope for example, a cancer lesion is observed by observation with a normal illumination light endoscope or a special light endoscope.
  • OCT measurement By finding and performing OCT measurement of the region, it is possible to determine how far the cancerous lesion has infiltrated. Further, by scanning the optical axis of the measurement light two-dimensionally, three-dimensional information can be acquired together with depth information obtained by OCT measurement.
  • Integrating OCT measurement and 3D computer graphic technology makes it possible to display a 3D structural model consisting of structural information to be measured with a resolution on the order of micrometers.
  • this three-dimensional structure model by OCT measurement is referred to as three-dimensional volume data.
  • the present invention has been made in view of such circumstances, and an optical tomographic imaging apparatus capable of clearly identifying a region (non-signal region) where light does not reach and no deep information is obtained in a tomographic image, and
  • An object is to provide an optical tomographic imaging method.
  • the optical tomographic imaging apparatus divides light emitted from a wavelength swept light source into measurement light and reference light, and uses the measurement light as a measurement object. Irradiate, combine the reflected light from the measurement object and the reference light, detect interference light when the reflected light and the reference light are combined as an interference signal, and use the interference signal to perform the measurement
  • a no-signal area where no reflected light is obtained from the measurement target is detected based on the interference signal, and a no-signal area image based on the detected no-signal area is constructed. Then, the no-signal area image is synthesized with the normal tomographic image.
  • the tomographic image it becomes possible to clearly identify a region where no deep information is obtained (no-signal region) where light does not reach, and a region where the mucosal muscle layer is not extracted is caused by the rupture of the mucosal muscle plate. It is possible to more reliably determine whether it is due to the fact that no interference light is detected. As a result, it becomes easier to determine whether cancer has invaded the mucosal lamina.
  • the no-signal area detection unit is a data obtained by performing Fourier transform and logarithmic transformation on the interference signal. It is preferable to include a smoothing processing unit that smoothes the data and a binarization processing unit that binarizes the data smoothed by the smoothing processing unit with a threshold value.
  • the smoothing processing unit includes a frame addition average processing unit, a line addition average processing unit, And a moving average processing unit.
  • the no-signal area detection unit is a data obtained by Fourier transforming and logarithmically transforming the interference signal. It is preferable that a non-signal pattern recognition processing unit for recognizing a random noise pattern at the time of no signal is provided.
  • the layer information of the measurement target is obtained based on the interference signal.
  • the optical tomographic imaging apparatus Like the optical tomographic imaging apparatus according to the sixth aspect of the present invention, the optical tomographic imaging apparatus according to the fifth aspect, wherein the image synthesis unit includes the tomographic image, the enhancement layer structure image, and the It is preferable to add and synthesize the non-signal area image at a preset ratio.
  • an optical tomographic imaging method divides light emitted from a wavelength swept light source into measurement light and reference light, and measures with the measurement light. Irradiate the object, combine the reflected light from the measurement object and the reference light, detect the interference light when the reflected light and the reference light are combined as an interference signal, and use the interference signal
  • An optical tomographic imaging method for obtaining a tomographic image of the measurement object, wherein a no-signal area detection step of detecting a no-signal area where no reflected light is obtained from the measurement object based on the interference signal; A non-signal area image construction step for constructing a non-signal area image based on the non-signal area detected in the signal area detection step; and an image synthesis step for synthesizing the tomographic image and the non-signal area image.
  • a no-signal area where no reflected light is obtained from the measurement object is detected based on the interference signal, and a no-signal area image based on the detected no-signal area is constructed. Then, the no-signal area image is synthesized with the normal tomographic image.
  • the tomographic image it becomes possible to clearly identify a region where no deep information is obtained (no-signal region) where light does not reach, and a region where the mucosal muscle layer is not extracted is caused by the rupture of the mucosal muscle plate. It is possible to more reliably determine whether it is due to the fact that no interference light is detected. As a result, it becomes easier to determine whether cancer has invaded the mucosal lamina.
  • the no-signal area detection step includes data obtained by Fourier transform and logarithmically transforming the interference signal. It is preferable to include a smoothing processing step for smoothing and a binarization processing step for binarizing the data smoothed by the smoothing processing step with a threshold value.
  • the smoothing processing step includes a frame addition average processing step, a line addition average processing step, And / or a moving average processing step.
  • the no-signal region detection step includes data obtained by Fourier transform and logarithmically transforming the interference signal. It is preferable to include a no-signal pattern recognition processing step for recognizing a random noise pattern during no signal.
  • the layer information of the measurement target is obtained based on the interference signal.
  • the image synthesizing step synthesizes the tomographic image, the no-signal area image, and the enhancement layer structure image.
  • the image synthesizing step includes the tomographic image, the enhancement layer structure image, and the no signal. It is preferable to add and combine the region images at a preset ratio.
  • the present invention it is possible to clearly identify a region (non-signal region) from which light does not reach and no deep information is obtained in the tomographic image, and the region from which the mucosal muscle layer is not extracted is the mucosal muscle plate. It is possible to more reliably determine whether it is due to the rupture of the beam or due to the fact that no interference light is detected. As a result, it becomes easier to determine whether cancer has invaded the mucosal lamina.
  • FIG. 1 is an external view showing an image diagnostic apparatus using the optical tomographic imaging apparatus according to the first embodiment
  • FIG. 2 is a block diagram showing the internal configuration of the OCT processor of FIG. 1
  • 3 is a cross-sectional view of the OCT probe of FIG. 2
  • FIG. 4 is a diagram showing a scan surface of a tomographic image when the optical scanning is radial scanning with respect to the measuring object S of FIG.
  • FIG. 5 is a diagram showing three-dimensional volume data constructed by the tomographic image of FIG. 4
  • 6 is a view showing a state in which a tomographic image is obtained using an OCT probe derived from the forceps opening of the endoscope of FIG. 1;
  • FIG. 1 is an external view showing an image diagnostic apparatus using the optical tomographic imaging apparatus according to the first embodiment
  • FIG. 2 is a block diagram showing the internal configuration of the OCT processor of FIG. 1
  • 3 is a cross-sectional view of the OCT probe of FIG. 2
  • FIG. 4 is
  • FIG. 7 is a diagram showing a configuration for obtaining a tomographic image by performing sector scanning on the measuring object S of FIG. 2;
  • FIG. 8 is a diagram showing three-dimensional volume data constructed by the tomographic image of FIG. 7;
  • FIG. 11 is a diagram showing an example of a tomographic image constructed by the tomographic image construction unit of FIG. 9;
  • 12 is a block diagram illustrating another configuration of the signal processing unit of FIG. 3;
  • FIG. 13 is a block diagram showing a configuration of a signal processing unit according to the second embodiment;
  • FIG. 14 is a diagram showing an example of a composite image generated by the image composition unit of FIG. 13;
  • FIG. 15 is a diagram illustrating an example of an intermediate image generated by the image composition unit of FIG.
  • FIG. 1 is an external view showing an image diagnostic apparatus using the optical tomographic imaging apparatus according to the first embodiment of the present invention.
  • the diagnostic imaging apparatus 10 mainly includes an endoscope 100, an endoscope processor 200, a light source device 300, an OCT processor 400 as an optical tomographic imaging device, and a monitor device 500.
  • the endoscope processor 200 may be configured to incorporate the light source device 300.
  • the endoscope 100 includes a hand operation unit 112 and an insertion unit 114 connected to the hand operation unit 112. The surgeon grasps and operates the hand operation unit 112 and performs observation by inserting the insertion unit 114 into the body of the subject.
  • the hand operation part 112 is provided with a forceps insertion part 138, and the forceps insertion part 138 communicates with the forceps port 156 of the distal end part 144.
  • the OCT probe 600 is led out from the forceps opening 156 by inserting the OCT probe 600 from the forceps insertion portion 138.
  • the OCT probe 600 is connected to the OCT processor 400 via the connector 610, the insertion portion 602 inserted from the forceps insertion portion 138 and led out from the forceps opening 156, the operation portion 604 for the operator to operate the OCT probe 600. Cable 606.
  • Endoscope At the distal end portion 144 of the endoscope 100, an observation optical system 150, an illumination optical system 152, and a CCD (not shown) are disposed.
  • the observation optical system 150 forms an image of a subject on a light receiving surface (not shown) of the CCD, and the CCD converts the subject image formed on the light receiving surface into an electric signal by each light receiving element.
  • the CCD of this embodiment is a color CCD in which three primary color red (R), green (G), and blue (B) color filters are arranged for each pixel in a predetermined arrangement (Bayer arrangement, honeycomb arrangement). is there.
  • reference numeral 154 denotes a cleaning nozzle for supplying a cleaning liquid and pressurized air toward the observation optical system 150.
  • the light source device 300 causes visible light to enter a light guide (not shown). One end of the light guide is connected to the light source device 300 via the LG connector 120, and the other end of the light guide faces the illumination optical system 152. The light emitted from the light source device 300 is emitted from the illumination optical system 152 via the light guide, and illuminates the visual field range of the observation optical system 150.
  • Endoscope processor An image signal output from the CCD is input to the endoscope processor 200 via the electrical connector 110.
  • the analog image signal is converted into a digital image signal in the endoscope processor 200, and necessary processing for displaying on the screen of the monitor device 500 is performed.
  • observation image data obtained by the endoscope 100 is output to the endoscope processor 200, and an image is displayed on the monitor device 500 connected to the endoscope processor 200.
  • FIG. 2 is a block diagram showing an internal configuration of the OCT processor of FIG.
  • An OCT processor 400 and an OCT probe 600 shown in FIG. 2 are for obtaining an optical tomographic image of a measurement object by an optical coherence tomography (OCT) measurement method, and emit a light La for measurement.
  • One light source unit (first light source unit) 12 and light La emitted from the first light source unit 12 are branched into measurement light (first light beam) L1 and reference light L2, and measurement is performed on the subject.
  • An optical fiber coupler (branching / combining unit) 14 that generates the interference light L4 by combining the return light L3 from the target S and the reference light L2, and the measurement light L1 branched by the optical fiber coupler 14 is guided to the measurement target.
  • an OCT probe 600 including a rotation-side optical fiber FB1 that guides the return light L3 from the measurement target, and guides the measurement light L1 to the rotation-side optical fiber FB1 and rotates the rotation-side optical fiber.
  • the fixed side optical fiber FB2 that guides the return light L3 guided by the bar FB1 and the rotation side optical fiber FB1 are rotatably connected to the fixed side optical fiber FB2, and the measurement light L1 and the return light L3 are transmitted.
  • the optical connector 18, the interference light detection unit 20 that detects the interference light L 4 generated by the optical fiber coupler 14 as an interference signal, and the interference signal detected by the interference light detection unit 20 to process the optical tomographic image ( Hereinafter, it is also simply referred to as “tomographic image”). Further, the optical tomographic image acquired by the signal processing unit 22 is displayed on the monitor device 500.
  • the OCT processor 400 adjusts the optical path length of the second light source unit (second light source unit) 13 that emits aiming light (second light flux) Le for indicating a mark of measurement, and the reference light L2.
  • An optical path length adjustment unit 26 an optical fiber coupler 28 that splits the light La emitted from the first light source unit 12, and detection units 30a and 30b that detect return lights L4 and L5 combined by the optical fiber coupler 14.
  • an operation control unit 32 that inputs various conditions to the signal processing unit 22, changes settings, and the like.
  • various lights including the above-described emission light La, aiming light Le, measurement light L1, reference light L2, return light L3, and the like are guided between components such as optical devices.
  • Various optical fibers FB (FB3, FB4, FB5, FB6, FB7, FB8, etc.) including the rotation side optical fiber FB1 and the fixed side optical fiber FB2 are used as light paths for wave transmission.
  • the first light source unit 12 emits light for measuring OCT (for example, laser light having a wavelength of 1.3 ⁇ m or low-coherence light), and the first light source unit 12 has a constant frequency. It is a light source that emits laser light La in the infrared region (for example, laser light having a wavelength of 1.3 ⁇ m at the center) while sweeping at a period.
  • the first light source unit 12 includes a light source 12a that emits laser light or low-coherence light La, and a lens 12b that condenses the light La emitted from the light source 12a.
  • the light La emitted from the first light source unit 12 is divided into the measurement light L1 and the reference light L2 by the optical fiber coupler 14 via the optical fibers FB4 and FB3, and the measurement light L1 is Input to the optical connector 18.
  • the second light source unit 13 emits visible light to make it easy to confirm the measurement site as the aiming light Le.
  • red semiconductor laser light having a wavelength of 0.66 ⁇ m, He—Ne laser light having a wavelength of 0.63 ⁇ m, blue semiconductor laser light having a wavelength of 0.405 ⁇ m, or the like can be used. Therefore, the second light source unit 13 includes, for example, a semiconductor laser 13a that emits red, blue, or green laser light, and a lens 13b that condenses the aiming light Le emitted from the semiconductor laser 13a.
  • the aiming light Le emitted from the second light source unit 13 is input to the optical connector 18 through the optical fiber FB8.
  • the measurement light L1 and the aiming light Le are combined and guided to the rotation side optical fiber FB1 in the OCT probe 600.
  • the optical fiber coupler (branching / combining unit) 14 is composed of, for example, a 2 ⁇ 2 optical fiber coupler, and is optically connected to the fixed-side optical fiber FB2, the optical fiber FB3, the optical fiber FB5, and the optical fiber FB7, respectively. ing.
  • the optical fiber coupler 14 divides the light La incident from the first light source unit 12 via the optical fibers FB4 and FB3 into measurement light (first light flux) L1 and reference light L2, and the measurement light L1 is fixed.
  • the light is incident on the optical fiber FB2, and the reference light L2 is incident on the optical fiber FB5.
  • the optical fiber coupler 14 is incident on the optical fiber FB5, is subjected to frequency shift and optical path length change by the optical path length adjusting unit 26 described later, and is returned by the optical fiber FB5 and acquired by the OCT probe 600 described later. Then, the light L3 guided from the fixed side optical fiber FB2 is multiplexed and emitted to the optical fiber FB3 (FB6) and the optical fiber FB7.
  • the OCT probe 600 is connected to the fixed optical fiber FB2 via the optical connector 18, and the measurement light L1 combined with the aiming light Le is rotated from the fixed optical fiber FB2 via the optical connector 18.
  • the light enters the side optical fiber FB1.
  • the measurement light L1 combined with the incident aiming light Le is transmitted by the rotation side optical fiber FB1, and is irradiated to the measurement object S.
  • the return light L3 from the measuring object S is acquired, the acquired return light L3 is transmitted by the rotation side optical fiber FB1, and is emitted to the fixed side optical fiber FB2 via the optical connector 18.
  • the optical connector 18 multiplexes the measurement light (first light beam) L1 and the aiming light (second light beam) Le.
  • the interference light detection unit 20 is connected to the optical fibers FB6 and FB7, and uses the interference lights L4 and L5 generated by combining the reference light L2 and the return light L3 by the optical fiber coupler 14 as interference signals. It is to detect.
  • the OCT processor 400 is provided on the optical fiber FB6 branched from the optical fiber coupler 28.
  • the detector 30a detects the light intensity of the interference light L4, and the light of the interference light L5 on the optical path of the optical fiber FB7. And a detector 30b for detecting the intensity.
  • the interference light detection unit 20 generates an interference signal based on the detection results of the detector 30a and the detector 30b.
  • the signal processing unit 22 acquires a tomographic image from the interference signal detected by the interference light detection unit 20, and outputs the acquired tomographic image to the monitor device 500.
  • a region where no reflected light is obtained from the measurement object S (no signal region) is detected based on the interference signal detected by the interference light detection unit 20, and no signal based on the no signal region is detected.
  • An area image is generated, and an image obtained by synthesizing the no-signal area image with the tomographic image is output to the monitor device 500.
  • a detailed configuration of the signal processing unit 22 for realizing this will be described later.
  • the optical path length adjusting unit 26 is arranged on the side of the optical fiber FB5 where the reference light L2 is emitted (that is, the end of the optical fiber FB5 opposite to the optical fiber coupler 14).
  • the optical path length adjustment unit 26 includes a first optical lens 80 that converts the light emitted from the optical fiber FB5 into parallel light, a second optical lens 82 that condenses the light converted into parallel light by the first optical lens 80, and The reflection mirror 84 that reflects the light collected by the second optical lens 82, the base 86 that supports the second optical lens 82 and the reflection mirror 84, and the base 86 are moved in a direction parallel to the optical axis direction.
  • the optical path length of the reference light L2 is adjusted by changing the distance between the first optical lens 80 and the second optical lens 82.
  • the first optical lens 80 converts the reference light L2 emitted from the core of the optical fiber FB5 into parallel light, and condenses the reference light L2 reflected by the reflection mirror 84 on the core of the optical fiber FB5.
  • the second optical lens 82 condenses the reference light L2 converted into parallel light by the first optical lens 80 on the reflection mirror 84, and makes the reference light L2 reflected by the reflection mirror 84 parallel light.
  • the first optical lens 80 and the second optical lens 82 form a confocal optical system.
  • the reflection mirror 84 is disposed at the focal point of the light collected by the second optical lens 82 and reflects the reference light L2 collected by the second optical lens 82.
  • the reference light L2 emitted from the optical fiber FB5 becomes parallel light by the first optical lens 80, and is condensed on the reflection mirror 84 by the second optical lens 82. Thereafter, the reference light L2 reflected by the reflection mirror 84 becomes parallel light by the second optical lens 82 and is condensed by the first optical lens 80 on the core of the optical fiber FB5.
  • the base 86 fixes the second optical lens 82 and the reflecting mirror 84, and the mirror moving mechanism 88 moves the base 86 in the optical axis direction of the first optical lens 80 (the direction of arrow A in FIG. 2). .
  • the distance between the first optical lens 80 and the second optical lens 82 can be changed, and the optical path length of the reference light L2 can be adjusted. Can do.
  • the operation control unit 32 has input means such as a keyboard and a mouse, and control means for managing various conditions based on the input information, and is connected to the signal processing unit 22.
  • the operation control unit 32 inputs, sets, and changes various processing conditions and the like in the signal processing unit 22 based on an operator instruction input from the input unit.
  • the operation control unit 32 may display the operation screen on the monitor device 500, or may provide a separate display unit to display the operation screen.
  • the operation control unit 32 controls the operation of the first light source unit 12, the second light source unit 13, the optical connector 18, the interference light detection unit 20, the optical path length, the detection units 30a and 30b, and sets various conditions. You may do it.
  • FIG. 3 is a cross-sectional view of the OCT probe of FIG.
  • the distal end portion of the insertion portion 602 has a probe outer cylinder 620, a cap 622, a rotation side optical fiber FB 1, a spring 624, a fixing member 626, and an optical lens 628. .
  • the probe outer cylinder (sheath) 620 is a flexible cylindrical member, and is made of a material through which the measurement light L1 combined with the aiming light Le and the return light L3 are transmitted in the optical connector 18.
  • the probe outer cylinder 620 is a tip through which the measurement light L1 (aiming light Le) and the return light L3 pass (the tip of the rotation side optical fiber FB1 opposite to the optical connector 18, hereinafter referred to as the tip of the probe outer cylinder 620). It is only necessary that a part of the side is made of a material that transmits light over the entire circumference (transparent material), and parts other than the tip may be made of a material that does not transmit light.
  • the cap 622 is provided at the tip of the probe outer cylinder 620 and closes the tip of the probe outer cylinder 620.
  • the rotation side optical fiber FB1 is a linear member, is accommodated in the probe outer cylinder 620 along the probe outer cylinder 620, is emitted from the fixed side optical fiber FB2, and is emitted from the optical fiber FB8 by the optical connector 18.
  • the measurement light L1 combined with the aiming light Le is guided to the optical lens 628, and the measurement object L is irradiated with the measurement light L1 (aiming light Le) to return from the measurement object S acquired by the optical lens 628.
  • the light L3 is guided to the optical connector 18 and enters the fixed optical fiber FB2.
  • the rotation-side optical fiber FB1 and the fixed-side optical fiber FB2 are connected by the optical connector 18, and are optically connected in a state where the rotation of the rotation-side optical fiber FB1 is not transmitted to the fixed-side optical fiber FB2. ing.
  • the rotation-side optical fiber FB1 is disposed so as to be rotatable with respect to the probe outer cylinder 620 and movable in the axial direction of the probe outer cylinder 620.
  • the spring 624 is fixed to the outer periphery of the rotation side optical fiber FB1.
  • the rotation side optical fiber FB1 and the spring 624 are connected to the optical connector 18.
  • the optical lens 628 is disposed at the measurement-side tip of the rotation-side optical fiber FB1 (tip of the rotation-side optical fiber FB1 opposite to the optical connector 18), and the tip is measured from the rotation-side optical fiber FB1.
  • the light L1 aiming light Le
  • it is formed in a substantially spherical shape.
  • the optical lens 628 irradiates the measurement target S with the measurement light L1 (aiming light Le) emitted from the rotation side optical fiber FB1, collects the return light L3 from the measurement target S, and enters the rotation side optical fiber FB1. .
  • the fixing member 626 is disposed on the outer periphery of the connection portion between the rotation side optical fiber FB1 and the optical lens 628, and fixes the optical lens 628 to the end portion of the rotation side optical fiber FB1.
  • the fixing method of the rotation side optical fiber FB1 and the optical lens 628 by the fixing member 626 is not particularly limited, and the fixing member 626, the rotation side optical fiber FB1, and the optical lens 628 are bonded and fixed by an adhesive. Alternatively, it may be fixed with a mechanical structure using bolts or the like.
  • the fixing member 626 may be any member as long as it is used for fixing, holding or protecting the optical fiber such as a zirconia ferrule or a metal ferrule.
  • the rotation side optical fiber FB1 and the spring 624 are connected to a rotation cylinder 656, which will be described later.
  • the optical lens 628 is moved to the probe outer cylinder 620.
  • the optical connector 18 includes a rotary encoder, and detects the irradiation position of the measurement light L1 from the position information (angle information) of the optical lens 628 based on a signal from the rotary encoder. That is, the measurement position is detected by detecting the angle of the rotating optical lens 628 with respect to the reference position in the rotation direction.
  • the rotation side optical fiber FB1, the spring 624, the fixing member 626, and the optical lens 628 are moved through the probe outer cylinder 620 in the arrow S1 direction (forceps opening direction) and the S2 direction (probe outer cylinder 620) by a driving unit described later. It is configured to be movable in the direction of the tip.
  • FIG. 3 is a diagram showing an outline of a drive unit such as the rotation side optical fiber FB1 in the operation unit 604 of the OCT probe 600.
  • the probe outer cylinder 620 is fixed to a fixing member 670.
  • the rotation side optical fiber FB1 and the spring 624 are connected to a rotating cylinder 656, and the rotating cylinder 656 is configured to rotate via a gear 654 in accordance with the rotation of the motor 652.
  • the rotary cylinder 656 is connected to the optical connector 18, and the measurement light L1 and the return light L3 are transmitted between the rotation side optical fiber FB1 and the fixed side optical fiber FB2 via the optical connector 18.
  • the frame 650 containing these is provided with a support member 662, and the support member 662 has a screw hole (not shown).
  • a forward and backward movement ball screw 664 is engaged with the screw hole, and a motor 660 is connected to the forward and backward movement ball screw 664. Therefore, the frame 650 can be moved forward and backward by rotationally driving the motor 660, whereby the rotation side optical fiber FB1, the spring 624, the fixing member 626, and the optical lens 628 can be moved in the S1 and S2 directions in FIG. It has become.
  • the OCT probe 600 is configured as described above, and the measurement side light L1 emitted from the optical lens 628 is obtained by rotating the rotation-side optical fiber FB1 and the spring 624 in the direction of the arrow R2 in FIG. (Aiming light Le) is irradiated to the measuring object S while scanning in the arrow R2 direction (circumferential direction of the probe outer cylinder 620), and the return light L3 is acquired.
  • the aiming light Le is irradiated to the measuring object S as, for example, blue, red, or green spot light, and the reflected light of the aiming light Le is also displayed as a bright spot on the observation image displayed on the monitor device 500.
  • a desired part of the measurement target S can be accurately captured and the return light L3 reflected from the measurement target S can be acquired over the entire circumference of the probe outer cylinder 620 in the circumferential direction.
  • the optical lens 628 is moved to the end of the movable range in the direction of the arrow S1 by the drive unit, and a predetermined amount is acquired while acquiring the tomographic images. Move to the end of the movable range while moving in the S2 direction or alternately repeating tomographic image acquisition and a predetermined amount of movement in the S2 direction.
  • a plurality of tomographic images in a desired range can be obtained for the measurement object S, and three-dimensional volume data can be obtained based on the acquired plurality of tomographic images.
  • FIG. 4 is a diagram showing a scan surface of a tomographic image when the optical scanning is radial scan with respect to the measurement target S of FIG. 2
  • FIG. 5 is a diagram showing three-dimensional volume data constructed by the tomographic image of FIG. It is.
  • a tomographic image in the depth direction (first direction) of the measurement target S is acquired from the interference signal, and the measurement target S is scanned (radial scan) in the direction of arrow R2 in FIG.
  • a tomographic image on the scan plane composed of the first direction and the second direction orthogonal to the first direction can be acquired.
  • a plurality of tomographic images for generating three-dimensional volume data can be acquired as shown in FIG.
  • FIG. 6 is a view showing a state in which a tomographic image is obtained using an OCT probe derived from the forceps opening of the endoscope shown in FIG.
  • the tomographic image is obtained by bringing the distal end portion of the insertion portion 602 of the OCT probe close to a desired portion of the measurement target S.
  • the optical lens 628 may be moved within the probe outer cylinder 620 by the drive unit described above.
  • FIG. 7 is a diagram illustrating a configuration in which a tomographic image is acquired by performing sector scanning on the measurement target S in FIG. 2, and FIG. 8 is a diagram illustrating three-dimensional volume data constructed from the tomographic image in FIG. .
  • the present invention can also be applied to a configuration in which a galvano mirror 900 is used and a sector scan is performed from above the measurement target S to acquire a tomographic image. As shown, a plurality of tomographic images for generating three-dimensional volume data can be acquired.
  • FIG. 9 is a block diagram showing a configuration of the signal processing unit 22 of FIG.
  • the signal processing unit 22 is a processing unit that performs signal processing for generating an image output to the monitor device 500 from the interference signal input from the interference light detection unit 20.
  • the Fourier transform unit 410, the logarithmic transformation unit 420, the smoothing processing unit 430, the binarization processing unit 440, the no-signal area image construction unit 450, the tomographic image construction unit 470, the image composition unit 480, and the control unit 490 are mainly provided. It is prepared for.
  • the control unit 490 controls each unit of the signal processing unit 22 based on the operation signal from the operation control unit 32.
  • the interference light detection unit 20 is obtained when the light emitted from the first light source unit 12 serving as a wavelength swept light source is divided into measurement light and reference light, and the measurement light S is irradiated from the OCT probe 600 to the measurement target S.
  • the interference light when the reflected light and the reference light are combined is input.
  • the interference light detection unit 20 converts an input interference light (optical signal) into an interference signal (electric signal), and converts the interference signal generated by the interference signal generation unit 20a from an analog signal to a digital signal. It comprises an AD conversion unit 20b that converts it into a signal.
  • the AD conversion unit 20b for example, conversion from an analog signal to a digital signal is performed with a resolution of about 14 bits at a sampling rate of about 80 MHz, but these values are not particularly limited.
  • the interference signal converted into a digital signal by the AD conversion unit 20 b is input to the Fourier transform unit 410 of the signal processing unit 22.
  • the Fourier transform unit 410 performs frequency analysis by FFT (Fast Fourier Transform) on the interference signal converted into a digital signal in the AD conversion unit 20b of the interference light detection unit 20, and the reflected light L3 at each depth position of the measurement target S. Intensity, that is, reflection intensity data (tomographic information) in the depth direction.
  • the data (tomographic information) Fourier-transformed by the Fourier transform unit 410 is logarithmically transformed by the logarithmic transform unit 420.
  • the logarithmically converted data is input to a smoothing processing unit 430 and a tomographic image construction unit 470 described later.
  • the logarithmically converted data is subjected to coordinate conversion according to the scanning method such as brightness, contrast adjustment, resampling according to the display size, radial scanning, sector scanning, etc., and output as a tomographic image.
  • the smoothing processing unit 430 performs a smoothing process on the logarithmically converted data.
  • the smoothing processing unit 430 may be configured by a three-dimensional smoothing filter unit, a two-dimensional smoothing filter unit alone or in combination with a one-dimensional filter unit, but a frame addition average processing unit 431, a line addition average processing unit 432, It is desirable that the moving average processing unit 433 is configured by one or more combinations.
  • the smoothing processing unit 430 of this example includes a frame addition average processing unit 431, a line addition average processing unit 432, and a moving average processing unit 433.
  • the frame addition average processing unit 431 performs smoothing by averaging data between frames.
  • any of simple frame addition averaging, weighted frame addition averaging, and cyclic frame correlation is desirable, but any generally known method may be used.
  • the number of frames to be added and averaged is not particularly limited.
  • Cyclic frame correlation is to generate frame data to be output by synthesizing new input frame data and current output frame data at a ratio of ⁇ : 1 ⁇ based on the following (Equation 1). Since this can be realized by securing a frame memory for one frame, there is an advantage that it can be realized with a smaller amount of memory than the frame addition average.
  • [OUT (n)] ⁇ ⁇ [IN] + (1 ⁇ ) ⁇ [OUT (n ⁇ 1)] ( ⁇ ⁇ 1) (Formula 1)
  • OUT (n) is the nth output frame data
  • IN is the new input frame data
  • OUT (n ⁇ 1) is the (n ⁇ 1) th output frame data, that is, the output frame data one frame before
  • ⁇ represents a frame correlation coefficient.
  • the line addition average processing unit 432 performs smoothing by averaging data between scan lines.
  • the method of the line addition averaging process simple addition averaging or weighted addition averaging is preferable, but any generally known method may be used. Further, the number of lines to be added and averaged is not particularly limited.
  • the moving average processing unit 433 performs smoothing by averaging the data in the depth direction.
  • any one of a simple moving average, a weighted moving average, and a digital low-pass filter is desirable, but any generally known method may be used.
  • the number of data points to be averaged is not particularly limited.
  • the binarization processing unit 440 performs binarization processing by comparing the data smoothed by the smoothing processing unit 430 with a predetermined threshold value.
  • the threshold value used at this time may be a fixed value set in advance, or may be input from the input means (for example, an operation panel) of the operation control unit 32 each time.
  • the no-signal area image construction unit 450 constructs a no-signal area image according to the monitor device 500 and its display method based on the data binarized by the binarization processing unit 440. More specifically, a no-signal area image is constructed by adjusting brightness and contrast, resampling in accordance with the display size, coordinate conversion in accordance with a scanning method such as radial scanning, sector scanning, and the like.
  • the tomographic image constructing unit 470 is a processing unit that constructs a normal tomographic image in the same manner as in the past, and receives the data logarithmically converted by the logarithmic converting unit 420, and the monitor device 500 and its display from the input data.
  • a tomographic image is constructed according to the method. Specifically, as with the no-signal area image construction unit 450, the tomographic image is constructed by adjusting the brightness and contrast, resampling to the display size, coordinate conversion according to the scanning method such as radial scanning, sector scanning, etc. To do.
  • the image composition unit 480 synthesizes the tomographic image constructed by the tomographic image construction unit 470 and the non-signal region image constructed by the no-signal region image construction unit 450.
  • image synthesis is not limited to these, and any commonly used method such as a method of superimposing a non-signal area image on a tomographic image may be used.
  • the synthesized image (synthesized image) is output to a monitor device 500 such as an LCD monitor.
  • the Fourier transform unit 410 performs frequency analysis by FFT (Fast Fourier Transform). Thereby, reflection intensity data (tomographic information) in the depth direction of the measuring object S is generated. That is, the layer information extraction unit in the optical tomographic imaging apparatus of the present invention can be realized mainly by the Fourier transform unit 410.
  • FFT Fast Fourier Transform
  • the tomographic information generated by the Fourier transform unit 410 is logarithmically converted by the logarithmic conversion unit 420 and further smoothed by the smoothing processing unit 430. Thereby, the noise component is removed from the tomographic information.
  • predetermined smoothing processing is sequentially performed by the frame addition average processing unit 431, the line addition average processing unit 432, and the moving average processing unit 433, respectively.
  • the data smoothed by the smoothing processing unit 430 that is, the tomographic information after removal of the noise component is input to the binarization processing unit 440, and binarization processing is performed by comparison with a predetermined threshold value.
  • the tomographic information after removing the noise component is separated into a region where the reflected light is obtained (signal region) and a region where the reflected light is not obtained (non-signal region).
  • the data binarized by the binarization processing unit 440 is input to the no-signal region image construction unit 450, and a no-signal region image is constructed based on the input data.
  • the data logarithmically converted by the logarithmic conversion unit 420 is also input to the tomographic image construction unit 470, and a normal tomographic image similar to the conventional one is constructed based on the inputted data.
  • the non-signal area image constructed by the no-signal area image construction unit 450 and the tomographic image constructed by the tomographic image construction unit 470 are synthesized by the image synthesis unit 480.
  • a composite image is generated by superimposing the no-signal area image on the tomographic image.
  • the composite image generated in this way by the image composition unit 480 is displayed on the monitor device 500 and can be diagnosed.
  • FIG. 10 shows the composite image generated by the image composition unit 480 displayed as it is without adding an auxiliary line
  • the part (b) of FIG. The portion () shows the composite image shown in the portion (a) with an auxiliary line representing the outline of the no-signal area image displayed.
  • the composite image shown in FIG. 10 shows a composite image obtained when sector scanning is performed from above the measurement target S using the galvanometer mirror 900 described in FIG.
  • the smoothing processing unit 430 a simple addition average of 8 frames in the frame addition average processing unit 431, a simple addition average of 8 lines in the line addition average processing unit 432, and a simple moving average of 21 points in the moving average processing unit 433.
  • FIG. 11 shows an example of a tomographic image constructed by the tomographic image construction unit 470 in FIG. 9 as a comparative example of the composite image shown in FIG.
  • the tomographic image shown in FIG. 11 is the same as the grayscale tomographic image obtained by the conventional OCT signal processing, and a normal tomographic image that becomes an original image when the composite image shown in FIG. 10 is generated is obtained. Show.
  • the method for detecting the non-signal area is not limited to the above-described example.
  • FIG. 12 is a block diagram showing another configuration of the signal processing unit 22 of FIG. In FIG. 12, the same reference numerals are assigned to components that are common or similar to those in FIG.
  • the signal processing unit 22B shown in FIG. 12 includes a no-signal pattern recognition processing unit 460 instead of the smoothing processing unit 430 and the binarization processing unit 440 of FIG.
  • the data subjected to logarithmic conversion by the logarithmic conversion unit 420 is subjected to recognition processing of a random noise pattern when there is no signal in the no-signal pattern recognition processing unit 460, whereby a no-signal region is detected. Then, based on the no-signal area detected by the no-signal pattern recognition processing unit 460, the no-signal area image construction unit 450 constructs a no-signal area image. Other processes are the same as those in FIG.
  • the recognition processing performed in the no-signal pattern recognition processing unit 460 is not particularly limited, and a generally known method can be used. For example, from the viewpoint of ease of processing, a method of recognizing a random noise pattern due to the absence of a specific frequency component in frequency analysis by two-dimensional FFT is preferable.
  • the second embodiment is an improvement of the first embodiment, and not only a non-signal area image is synthesized with a normal tomographic image but also an enhanced layer structure image (differential image) in which the layer structure is emphasized. Are combined and displayed. This makes it possible to easily identify the layer structure such as the mucosal lamina layer, whether the area where the mucosal lamina layer has not been extracted is due to the rupture of the mucosal lamina, or because the interference light is not detected. It becomes possible to judge more reliably.
  • FIG. 13 is a block diagram showing a configuration of a signal processing unit according to the second embodiment.
  • elements that are the same as or similar to those in FIG. 13 are the same as or similar to those in FIG.
  • the signal processing unit 22C as the second embodiment further includes a smoothing processing unit 710, a differential processing unit 720, and a differential signal.
  • a smoothing processing unit 730 and a differential image construction unit 740 are provided.
  • the smoothing processing unit 710 performs a smoothing process on the data logarithmically converted by the logarithmic conversion unit 420.
  • the smoothing processing unit 710 has the same configuration as that of the smoothing processing unit 430. As illustrated in FIG. 3, the smoothing processing unit 710 includes one of a frame addition average processing unit 431, a line addition average processing unit 432, and a moving average processing unit 433. It is desirable to be configured by a combination of two or more.
  • the smoothing processing unit 430 and the smoothing processing unit 710 are shown as different functional blocks. However, it is needless to say that these may be integrated into one functional block. In this case, since the signal processing unit 22C has a simple configuration, the cost can be reduced.
  • the differentiation processing unit 720 performs differentiation processing in the depth direction on the data smoothed by the smoothing processing unit 710. Thereby, a differential signal as a feature value is acquired. That is, the feature amount calculation unit in the optical tomographic imaging apparatus of the present invention can be realized mainly by the differentiation processing unit 720.
  • the differential processing performed at this time is not particularly limited because it is generally known, but as an example, there is a method of calculating a difference for each data point in the depth direction.
  • the differential signal smoothing processing unit 730 performs the smoothing process by averaging the differential signals in the depth direction. Thereby, the noise component contained in the differential signal as the feature quantity is removed.
  • a smoothing processing method any one of a simple moving average, a weighted moving average, and a digital low-pass filter is desirable, but any generally known method may be used.
  • the number of data points to be averaged is not particularly limited.
  • the differential image construction unit 740 constructs a differential image as an enhanced layer structure image in accordance with the monitor device 500 and its display method from the smoothed differential signal. Specifically, the differential image is constructed by adjusting the brightness and contrast, resampling in accordance with the display size, coordinate conversion in accordance with a scanning method such as radial scanning and sector scanning. As described above, the enhancement layer structure image construction unit in the optical tomographic imaging apparatus of the present invention can be realized mainly by the differential image construction unit 740.
  • the image composition unit 480 synthesizes the tomographic image constructed by the tomographic image construction unit 470, the non-signal region image constructed by the no-signal region image construction unit 450, and the differential image constructed by the differential image construction unit 740. Then, the synthesized image is output to the monitor device 500.
  • the image composition method in the image composition unit 480 is preferably a method in which a tomographic image, a differential image, and a no-signal area image are added and combined at a preset ratio. Specifically, as a method of combining the tomographic image, the differential image, and the no-signal area image, (1) A method of adding a differential image with a constant ratio ⁇ and a non-signal area image with a constant ratio ⁇ when the tomographic image is set to 1.
  • Composite image tomographic image + ⁇ ⁇ differential image + ⁇ ⁇ non-signal area Image (0 ⁇ ⁇ 1)
  • the image synthesis method is not limited to these, and any commonly used method such as a method of superimposing a differential image or a no-signal area image on a tomographic image is used. Also good.
  • a composite image output from the image combining unit 480 is generated by combining the tomographic image, the differential image, and the no-signal area image.
  • the composite image output from the image composition unit 480 is displayed on the monitor device 500 and can be diagnosed.
  • FIG. 14 an example of the composite image generated by the image composition unit 480 of FIG. 13 is shown in FIG.
  • the composite image shown in FIG. 14 is an intermediate image (FIG. 14) obtained by adding the differential images constructed by the differential image construction unit 740 at a ratio of 0.2, assuming that the tomographic image shown in FIG. 15), a non-signal region image constructed by the non-signal region image construction unit 450 is superimposed on the image.
  • FIGS. 14 and 15 all are displayed in gray scale due to the limitations of the drawings.
  • the signal area image and the differential image are displayed in different colors.
  • the no-signal area image is displayed in red
  • the differential image that is, the mucosal muscle layer
  • auxiliary lines are added and displayed at positions or ranges corresponding to the differential image and the no-signal area image.
  • the central line (broken line in the figure) along the horizontal direction is the mucosal muscularis mucosa, and the part cut off at the center of this line is destroyed by the invasion of cancer. It is a part that has been.
  • the differential image construction unit 740 it is preferable to extract only positive components that exceed a predetermined threshold, for example, 0, from the smoothed differential signal, and image them to construct a differential image. As a result, a layer structure such as a mucosal muscle plate can be depicted more clearly. Furthermore, it is more preferable that the differential image is a color image using a preset color map, and the target structure can be recognized more easily.
  • a predetermined threshold for example, 0, from the smoothed differential signal
  • the synthesized image displayed on the monitor device 500 has information on the layer structure such as the mucosal muscle layer.
  • a layer structure such as a mucosal muscle layer can be easily identified.
  • it is possible to more reliably determine whether the region from which the mucosal muscle layer has not been extracted is due to the tear of the mucosal muscle or whether the interference light is not detected.
  • the SS-OCT (Swept Source OCT) apparatus has been described as the OCT processor 400.
  • the present invention is not limited to this, and the OCT processor 400 can also be applied as an SD-OCT (SpectralDomain OCT) apparatus. Is possible.
  • optical tomographic imaging apparatus and optical tomographic imaging method of the present invention have been described in detail above, but the present invention is not limited to the above examples, and various improvements and modifications can be made without departing from the spirit of the present invention. Of course, deformation may be performed.

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Abstract

Dans un dispositif de tomographie optique, un processeur de signal (22) d'un processeur OCT (400) génère des informations de section transversale à partir d'un signal d'interférence au moyen d'une unité de transformée de Fourier (410), enlève les composants de bruit des informations de section transversale au moyen d'une unité de transformée logarithmique (420) et un processeur de lissage (430), et détecte les régions vides de signal en effectuant le traitement de binarisation sur les informations de section transversale au moyen d'un processeur de binarisation (440) une fois les composants de bruit enlevés. Une image de région vide de signal sur la base des régions vides de signal est construite dans un constructeur (450) d'image de région vide de signal, l'image de région vide de signal est synthétisée par un synthétiseur d'image (480) avec une image de section transversale construite séparément, l'image synthétisée étant sortie vers un moniteur (500).
PCT/JP2011/063640 2010-06-15 2011-06-15 Dispositif de tomographie optique et procédé de tomographie optique Ceased WO2011158848A1 (fr)

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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN110063714A (zh) * 2018-01-22 2019-07-30 株式会社多美 光学相干层析成像装置

Families Citing this family (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US11382516B2 (en) * 2018-06-08 2022-07-12 Canon U.S.A., Inc. Apparatuses, methods, and storage mediums for lumen and artifacts detection in one or more images, such as in optical coherence tomography images
US11361481B2 (en) * 2019-09-18 2022-06-14 Topcon Corporation 3D shadow reduction signal processing method for optical coherence tomography (OCT) images

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2004528111A (ja) * 2001-04-30 2004-09-16 ザ・ジェネラル・ホスピタル・コーポレイション 焦点特性とコヒーレンス・ゲートを制御するために動的フィードバックを用いた、光干渉トモグラフィにおける写像性と感度を改善するための方法及び装置
JP2008039651A (ja) * 2006-08-09 2008-02-21 Univ Of Tsukuba 光断層画像の処理方法
JP2009293998A (ja) * 2008-06-03 2009-12-17 Shofu Inc 干渉断層撮影装置
JP2010110556A (ja) * 2008-11-10 2010-05-20 Canon Inc 画像処理装置、画象処理方法、プログラム、及びプログラム記憶媒体
JP2010181172A (ja) * 2009-02-03 2010-08-19 Topcon Corp 光画像計測装置

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2004528111A (ja) * 2001-04-30 2004-09-16 ザ・ジェネラル・ホスピタル・コーポレイション 焦点特性とコヒーレンス・ゲートを制御するために動的フィードバックを用いた、光干渉トモグラフィにおける写像性と感度を改善するための方法及び装置
JP2008039651A (ja) * 2006-08-09 2008-02-21 Univ Of Tsukuba 光断層画像の処理方法
JP2009293998A (ja) * 2008-06-03 2009-12-17 Shofu Inc 干渉断層撮影装置
JP2010110556A (ja) * 2008-11-10 2010-05-20 Canon Inc 画像処理装置、画象処理方法、プログラム、及びプログラム記憶媒体
JP2010181172A (ja) * 2009-02-03 2010-08-19 Topcon Corp 光画像計測装置

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN110063714A (zh) * 2018-01-22 2019-07-30 株式会社多美 光学相干层析成像装置
CN110063714B (zh) * 2018-01-22 2023-12-29 株式会社多美 光学相干层析成像装置

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